JPS6040069A - Catheter having deformable soft leading end - Google Patents

Catheter having deformable soft leading end

Info

Publication number
JPS6040069A
JPS6040069A JP58212297A JP21229783A JPS6040069A JP S6040069 A JPS6040069 A JP S6040069A JP 58212297 A JP58212297 A JP 58212297A JP 21229783 A JP21229783 A JP 21229783A JP S6040069 A JPS6040069 A JP S6040069A
Authority
JP
Japan
Prior art keywords
catheter
catheter according
tip
distal end
sleeve
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
JP58212297A
Other languages
Japanese (ja)
Other versions
JPH0128588B2 (en
Inventor
ロバート　エイ．バン　タツセル
マーク　エイ．ライデル
ギルモアー　テー．スクジエルダール
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
ANGIOMEDEITSUKUSU Inc
Original Assignee
ANGIOMEDEITSUKUSU Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by ANGIOMEDEITSUKUSU Inc filed Critical ANGIOMEDEITSUKUSU Inc
Publication of JPS6040069A publication Critical patent/JPS6040069A/en
Publication of JPH0128588B2 publication Critical patent/JPH0128588B2/ja
Granted legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0067—Catheters; Hollow probes characterised by the distal end, e.g. tips
    • A61M25/0068—Static characteristics of the catheter tip, e.g. shape, atraumatic tip, curved tip or tip structure
    • A61M25/0069—Tip not integral with tube
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters
    • A61M25/1011—Multiple balloon catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056—Transvascular endocardial electrode systems

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Biomedical Technology (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Pulmonology (AREA)
  • Hematology (AREA)
  • Anesthesiology (AREA)
  • Biophysics (AREA)
  • Child & Adolescent Psychology (AREA)
  • Vascular Medicine (AREA)
  • Cardiology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Media Introduction/Drainage Providing Device (AREA)

Abstract

(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

【発明の詳細な説明】 本発明は一般的に生体内に導入されるようＫしたカテー
テル構造に関し、さらに詳しく言えば内皮組織に最小の
損害または外傷をもって患者の血管系統を通って導入さ
れ通路を作って進むことができるカテーテルの設計に関
する。DETAILED DESCRIPTION OF THE INVENTION The present invention relates generally to catheter structures adapted to be introduced in vivo, and more particularly to catheter structures adapted to be introduced and passaged through a patient's vascular system with minimal damage or trauma to the endothelial tissue. Concerning the design of catheters that can be made and advanced.

現今の外科治療法は管状のカテーテルが人体の血管系統
内に導入されることを許す１１例えば、血管造影カテー
テルは普通大腿部動脈に導入され動脈系統の中を通路な
作って進み冠状石門に達するので、放射線不透過性コン
トラスト剤または薬剤が診断または治療法として注入さ
れることができる。典型的な場合は、そのようなカテー
テルはカテーテルが通過しなければならない管の断面よ
り相当小さい前身て決められた小さい直径の長い弾性の
あるプラスティック管を含む。本発明が用いる他の形態
のカテーテルは心臓病のベース・メーカと関連するカテ
ーテルである。ここでは、カテーテルは典型的な場合と
して鎖骨下動脈を通りまた大静脈を通って心臓の右側の
心室に入るようにされる。またカテーテルは心内膜心臓
組織に接触するようＫされた１個またはより多くの表面
電極内にカテーテルの遠位末端で終る長い導体を取り囲
む弾性鞘の形をとる。Current surgical treatment methods allow tubular catheters to be introduced into the body's vascular system.11 For example, angiography catheters are commonly introduced into the femoral artery and are passed through the arterial system to the coronary artery. radiopaque contrast agents or agents can be injected as a diagnostic or therapeutic method. Typically, such catheters include a long elastic plastic tube of a predetermined small diameter that is considerably smaller than the cross-section of the tube through which the catheter must pass. Another form of catheter used by the present invention is a catheter associated with a cardiac base manufacturer. Here, the catheter is typically passed through the subclavian artery and through the vena cava into the right ventricle of the heart. The catheter also takes the form of an elastic sheath surrounding a long conductor that terminates at the distal end of the catheter within one or more surface electrodes adapted to contact endocardial heart tissue.

従来の技術では、血管造影用及び他の診断用カテーテル
並びに心臓病のベースメーカ・リード線は一般忙ポリエ
チレン、ポリウレタン、ポリゾロピレンまたはシリコン
・ラバーまたは非トｐンポゲン材料から一般に成形され
る。これらのものは血管血統を折り曲がったり挫屈した
りすることなしに通されるので、カテーテルの遠位末端
が鈍〜・刃先または鋭い刃先を持つだ場合特に血管組織
に損傷を与えることのできる壁の厚さと硬度を有しなけ
ればならない。恐らくまれであろうが、鋭い刃を有する
小さい直径のカテーテルが大動脈の壁を貫通して患者を
死に到らしめるという例があった。In the prior art, angiographic and other diagnostic catheters and cardiac base manufacturer leads are commonly molded from conventional polyethylene, polyurethane, polyzolopyrene or silicone rubber or non-topogenic materials. These are passed through the vascular lineage without bending or buckling the wall, which can damage the vascular tissue, especially if the distal end of the catheter has a blunt or sharp cutting edge. thickness and hardness. Although probably rare, there have been instances where small diameter catheters with sharp edges have penetrated the wall of the aorta, resulting in the death of a patient.

本発明はある従来の技術によるカテーテルに本質的にあ
る上記の問題をカテーテルの遠位末端に取り付けた軟ら
かい変形可能な部品を含むことによって緩和する。１つ
の実施例では、変形可能な先端部品はカテーテルの比較
的硬い先端を有する遠位末端に取り付けた環状のふくら
ますことができ弾性のある非膨張性の６風船１部７品を
含む。この構造ではカテーテル自身はカテーテルのほと
んど“全長にわたって延びて変形可能な先端部品と導通
ずる内腔を備え、それによ？パて流体はカテーテルの先
端部の大きさ、形状及び強固さを制御するため導入され
ることができる。風船状先端を選択的にふくらますこと
により、先端の有効面積は。The present invention alleviates the above problems inherent in certain prior art catheters by including a soft deformable component attached to the distal end of the catheter. In one embodiment, the deformable tip component includes an annular inflatable, elastic, non-inflatable 6-part balloon attached to the relatively stiff tipped distal end of the catheter. In this construction, the catheter itself has a lumen that extends almost the entire length of the catheter and communicates with the deformable tip piece, allowing fluid to control the size, shape, and stiffness of the catheter tip. By selectively inflating the balloon-like tip, the effective area of the tip can be increased.

カテーテルの先端と血管との間の接触点での単位面積当
りの全体の力を減小させるよう大きくすることができる
。It can be increased to reduce the overall force per unit area at the point of contact between the tip of the catheter and the blood vessel.

第２の実施例では、軟らかい変形可能な先端部品はカテ
ーテルの剛性のある先端を取り囲み１通常カテーテルを
越えて前以て決められた距離だけ延びる環状のプラステ
ィックまたはイムのスリーブを含む。スリーブの厚さま
たは構成は、スリーブの終端が人体組織におしつけられ
るときスリーブの折り曲がりまたは挫屈の好適な位置を
与えるよう２円周線に沿って変更される。スリーブが挫
屈させられ、変形可能な先端と□人体組織の間の有効接
触面積が増加して１組織に加えられる単位面積当りの圧
力または力を再び小さくする。In a second embodiment, the soft deformable tip piece includes an annular plastic or im sleeve that surrounds the rigid tip of the catheter and extends a predetermined distance, usually beyond the catheter. The thickness or configuration of the sleeve is varied along two circumferential lines to provide a preferred location for folding or buckling of the sleeve as the terminal end of the sleeve is imprinted on body tissue. The sleeve is buckled, increasing the effective contact area between the deformable tip and body tissue, again reducing the pressure or force per unit area applied to the tissue.

よって医療用の新しい改良されたカテーテル構造を提供
することは本発明の主たる目的である。It is therefore a principal object of the present invention to provide a new and improved catheter structure for medical use.

本発明のもう１つの目的は、軟らかい変形可能な先端を
有し、それによってカテーテルが血管系統に導入されそ
の中に通路を作って進むとき血管組織に損傷を与える可
能性を小さくするカテーテルを提供することである。Another object of the present invention is to provide a catheter having a soft deformable tip, thereby reducing the potential for damage to vascular tissue as the catheter is introduced and tunneled into the vascular system. It is to be.

本発明のさらに他の目的は、ふくらますことのできる先
端部品を有し、それによってカテーテルの遠位末端の形
状と強固さがカテーテルの手前の端に流体が導入される
ことによって制御されることのできるカテーテルを提供
することである。Yet another object of the invention is to have an inflatable tip component whereby the shape and stiffness of the distal end of the catheter is controlled by the introduction of fluid into the proximal end of the catheter. The purpose of the present invention is to provide a catheter that can be used.

本発明のさらに別の目的は、変形できる先端部品が遠位
末端及びそれが接触する人体組織との間の全体としての
接触面積を効果的に増加させる目的で、予見できる挫屈
をするよう前以て決められた壁の厚さの輪郭を有し、ス
リーブ形の軟らかい変形できる先端を付けたカテーテル
を提供することである。Yet another object of the invention is that the deformable tip component is pre-configured to undergo foreseeable buckling for the purpose of effectively increasing the overall contact area between the distal end and the body tissue with which it contacts. It is an object of the present invention to provide a catheter having a defined wall thickness profile and a sleeve-shaped soft deformable tip.

本発明のこれらの目的及び他の目的と利点はこの技術に
練達の人には以下の好適な実施例の詳細な記載から、特
に添付図面を参照して考察されたとき明白になるであろ
う。添付図面では同じ誉号はいくつかの図で相当する部
品に対して用いられる。These and other objects and advantages of the present invention will become apparent to those skilled in the art from the following detailed description of the preferred embodiment, particularly when considered with reference to the accompanying drawings. . In the accompanying drawings, the same honorifics are used for corresponding parts in several figures.

まず第１図を参照して、典型的な従来の技術による血管
造影カテーテルの遠位末端部分の縦方向の断面が示され
る。図では手前の末端（図示しない）から遠位末端１２
までカテーテルの全長にわたって延びる中央内腔１１を
有する弾性プラスティック管１０の前以て決められた長
さを有するところが示される。内腔１１は、血管造影染
料または他の薬品が人体の外側に位置する手前の末端に
おいてカテーテルに導入することができまたカテーテル
の遠位末端１２が位置する人体内の前以て決められた場
所に内腔を通って流されることができるように設けられ
ている。Referring first to FIG. 1, a longitudinal cross-section of the distal end portion of a typical prior art angiography catheter is shown. In the figure, from the near end (not shown) to the distal end 12
It is shown having a predetermined length of elastic plastic tube 10 with a central lumen 11 extending the entire length of the catheter. The lumen 11 allows angiographic dyes or other agents to be introduced into the catheter at the proximal end located outside the body and at a predetermined location within the body where the distal end 12 of the catheter is located. is provided so that it can be flowed through the lumen.

従来の技術による第１図のカテーテルの遠位先端２は比
較的鋭い突然切れる端１３において終り。The distal tip 2 of the prior art catheter of FIG. 1 terminates in a relatively sharp, abrupt end 13.

また、カテーテル１０の本体に使用される物質のタイプ
によって、遠位先端は血管組織、特にカテーテルが血管
系統の中に通路を作って進むとき血管の裏うちをする内
皮層（内膜）に損傷を起こすに充分な剛性を持っている
ことを特に注目すべきである。Also, depending on the type of material used in the body of the catheter 10, the distal tip may damage the vascular tissue, particularly the endothelial layer (intima) that may line the blood vessel as the catheter navigates its way through the vascular system. It is particularly noteworthy that it has sufficient stiffness to cause

この問題を緩和するために、第２図に示す本発明の第１
の実施例に従って、カテーテルの本体１０゛は二重の内
腔、即ち血管造影染料または他の流体を流すことを許す
内腔１１とさらにカテーテルの全長にわたってまた延び
る内腔１４を備える。In order to alleviate this problem, the first method of the present invention shown in FIG.
According to this embodiment, the body 10' of the catheter comprises a dual lumen, a lumen 11 which allows the flow of angiographic dye or other fluid, and a lumen 14 which also extends over the entire length of the catheter.

弾性を有し膨張しないふくらますことのできる１風船部
品″１５がカテーテル本体の遠位末端１４にしっかりと
取り付けられ、″風船部品”は、ふくらませられたとき
の形では、ドーナツの形を一般的にしている。内腔１４
は先端１５を含む隆起の内側と導通し、一方内腔１１は
その環の中央の開口１７と導通する。内腔１１にカテー
テルの遠位末端のところで導入される流体は終局的には
、軟らかい弾性の先端１５の開口１７を通って外側に流
出されるが、内腔１４に導入される流体は環状室１６の
中に流れ、先端部品をふくらませる。先端部品１５は好
適の例として、二軸方向または架橋ポリオレフィン・フ
ィルムから形成され。A resilient, non-inflatable, inflatable balloon component "15" is securely attached to the distal end 14 of the catheter body, the "balloon component" having a generally donut shape when inflated. lumen 14
communicates with the inside of the ridge containing the tip 15, while the lumen 11 communicates with the central opening 17 of the ring. Fluid introduced into lumen 11 at the distal end of the catheter will eventually flow outwardly through opening 17 in soft elastic tip 15, whereas fluid introduced into lumen 14 will flow through the annular chamber. 16 and inflates the tip part. The tip piece 15 is preferably formed from a biaxial or crosslinked polyolefin film.

ｏ、ｏ　ｏ　ｏ　ｉインチ（０，００２５４１２Ｉ）か
ら０．００２５インチ（０，０６３５期）の範囲の厚さ
を持つことができる。このとき、ふくらませられていな
いと＠または内部の気体を抜き去られると。It can have a thickness ranging from 0.0025 inch (0.0025 inch) to 0.0025 inch (0.0635 inch). At this time, if it is not inflated, the gas inside will be removed.

それは剛性を欠きカテーテル本体１０の端部な包みその
形状にほぼ従う。しかしながら、一度正規に加圧される
と、カテーテルの端と、それが人体内に通路を作って進
みまたは人体内圧位置するときそれが突き当たる人体組
織との間の所望の有効面積を増加するようにふくらむ。It lacks rigidity and generally conforms to the shape of the end wrapper of catheter body 10. However, once properly pressurized, it increases the desired effective area between the end of the catheter and the body tissue it encounters when it is passaged into the human body or positioned within the human body. Swells up.

ふくらみの程度は勿論先端の軟らかさまたは変形の可能
性を決定する。かくして、医師はカテーテルの先端の性
質に対して相当の制御を行なうことができるので組織の
損傷は最小に止まるであろう。The degree of bulge, of course, determines the softness or deformability of the tip. Thus, the physician has considerable control over the properties of the catheter tip and tissue damage will be minimized.

ドーナツ形の風船１５は好適な例としてカテーテル本体
１０から別に離して造屋され１次いでカテーテル本体に
熱または化学的結合によって取り付けられるが、然し圧
力流体で満たされたとき。The donut-shaped balloon 15 is preferably constructed separately from the catheter body 10 and then attached to the catheter body by heat or chemical bonding, but when filled with pressurized fluid.

カテーテルの壁部自身をして出っ張らせられるカテーテ
ルの遠位末端の壁部に形成される空隙であってもよい。It may be a void formed in the wall of the distal end of the catheter that extends through the catheter wall itself.

第３図は第２図の実施例の別の形態を示し、これは膨張
させることのできない先端部品１５の内圧を制御するた
め膨張させることのできる弾性高分子材料スリーブ１８
を含むよう変更されている。FIG. 3 shows an alternative form of the embodiment of FIG. 2, which is an inflatable resilient polymeric sleeve 18 to control the internal pressure of the non-inflatable tip piece 15.
has been modified to include.

膨張させることのできる弾性高分子材料スリーブ１８は
カテーテル本体１０の全長に沿うどの位置にでも位置さ
せることができ、また、事実、カテーテルが通路を作っ
て進むとき挿入されたあと人体の外側に留まる位置にあ
るようカテーテルの最も手前の端に置かれることができ
る。弾性高分子材料スリーブは好適な場合カテーテル本
体１０の外側の表面内に形成されるリング状の窪み内に
置かれて、それぞれ１９と２０で示すカテーテルの端の
縁でカテーテル本体に流体が漏れない仕方で適合に接合
される。半径方向の円形穴２１がカテーテル本体の窪ん
だ表面から第２の内腔１４に延びる。半径方向の円形穴
２１並びにその穴より遠位にある内腔１４の部分と変形
することのできる先端１５０室１６は圧縮できない流体
によって満たされ、また適当な栓２２が半径方向の円形
の穴２１より手前にあるある点のところで内腔１４の中
に置かれる。The inflatable elastic polymeric material sleeve 18 can be positioned anywhere along the length of the catheter body 10 and, in fact, remains outside the human body after being inserted as the catheter is navigated. can be placed at the proximal end of the catheter so that it is in position. The resilient polymeric material sleeve is preferably placed within a ring-shaped recess formed in the outer surface of the catheter body 10 to prevent fluid from leaking into the catheter body at the end edges of the catheter, indicated at 19 and 20, respectively. It is joined in a suitable manner. A radial circular hole 21 extends from the recessed surface of the catheter body into the second lumen 14. The radial circular hole 21 as well as the portion of the lumen 14 distal to the hole and the deformable tip 150 chamber 16 are filled with an incompressible fluid and a suitable plug 22 is inserted into the radial circular hole 21. It is placed into the lumen 14 at some point more proximally.

第６図の先端部品１５に力が加えられると、この先端部
品の内圧は増加し１弾性高分子材料スリーグ１８の膨張
とそれに対応する先端部品１５の収縮を起こす。収縮の
程度は勿論加えられた力に比例し、収縮は続いて弾性高
成子材料スリーブ１８の′剛性′の画数である。先１瑞
部品の容積が減小することは結果として先端部品とそれ
がおしつけられる結合表面との間の接触面積を大きくす
ることになる。When a force is applied to the tip piece 15 of FIG. 6, the internal pressure of this tip piece increases, causing expansion of the elastic polymeric material sled 18 and corresponding contraction of the tip piece 15. The degree of contraction is, of course, proportional to the applied force, and the contraction is in turn a stroke of the ``stiffness'' of the sleeve 18 of elastic polymeric material. Reducing the volume of the tip piece results in a larger contact area between the tip piece and the bonding surface to which it is pressed.

スリーブ１８が人体の外部の一点に位置するときは、ス
リーブの膨張を起こすシステム内の流体圧を直接示す変
換器に適当に接続できる。When the sleeve 18 is located at a point outside the human body, it can be suitably connected to a transducer that directly indicates the fluid pressure within the system that causes expansion of the sleeve.

第３図の先端部品に絶えず注意を払って、環状の開口１
７を画定するため例えば２３のところにより厚いドーナ
ツ形をしたリングを一体に含むことが有利であることが
分っている。このリングは。Paying constant attention to the tip part of FIG.
It has been found advantageous to integrally include a thicker donut-shaped ring, for example at 23, to define 7. This ring.

カテーテルを入れるとき通されねばならないどのような
導入器の内径より大きくない外径を有する。It has an outer diameter that is no larger than the inner diameter of any introducer through which the catheter must be threaded.

この構造を使うと、先端部品１５は、先端部品１５の一
杯に延ばした直径より小さい内腔の形状に従うであろう
。何故ならば、壁部にかかる力が増加すると、先端部品
内の内圧は弾性高成子材料スリーブ１８の膨張によって
減小するからである。Using this configuration, tip piece 15 will conform to the shape of a lumen that is smaller than the fully extended diameter of tip piece 15. This is because as the force on the wall increases, the internal pressure within the tip component decreases due to expansion of the elastic polymeric material sleeve 18.

実際に使うときは、内腔１４は、先端部品１５から半径
方向の側方ポート２１を通りまた含んでのび、０．００
２インチ（０，０５３ＥＩ）から肌００４インチ（０，
１ｍ１）の範囲の直径を有する。内腔１４は９弾性高分
子材料スリーブ１８とそれが含む側方ポート２１が置か
れるカテーテルの手前の端まで連続させることができる
。In actual use, the lumen 14 extends from the tip piece 15 through and including the radial side ports 21 and has a diameter of 0.00 mm.
2 inches (0,053EI) to skin 004 inches (0,
1 m1). The lumen 14 can be continued to the proximal end of the catheter where the 9 elastic polymeric material sleeve 18 and its containing side port 21 are placed.

第２図の実施例のように、先端部品１５は好適な例とし
て延びないポリオレフィン膜から形成され０．００１イ
ンチ（０，０２５１１１）から０．００２５インチ（０
，０６６Ｍ＆）の範囲の厚さを持つことができる。これ
らの寸法と材料はここに例としてだげ紹介するもので、
必ずしも本発明の範囲を限定すると考えるべきではない
。As in the embodiment of FIG. 2, tip piece 15 is preferably formed from a non-extending polyolefin membrane and is 0.001 inch (0.025111) to 0.0025 inch (0.0025 inch).
,066M&). These dimensions and materials are provided here as an example only.
It should not necessarily be considered as limiting the scope of the invention.

第４図を参照して、こ＼には軟らかい変形可能なカテー
テルに取り付けた遠位末端を有するカテーテルの別の好
適な実施例が示される。第４図に示されるように、・こ
の先端部品はカテーテル本体１０の遠位末端を囲み１重
ね接手によってこの末端に嵌合する管形のスリーブ２４
を含み、スリーブ２４は前以て決められた長さでカテー
テルの遠位末端を越えて延びる。弾性のあるプラスチッ
ク・スリーブ２４の壁部は、一定の厚さであるよりむし
ろスリーブの最も遠い先端即ち終端２５が前以て決めら
れた小さい力が静止する物体におしつけられたとき、第
５図に示す形状に挫屈して神代するような形に形成され
ている。より詳しく述べれば、カテーテル１０の端を越
えて延びる先端部品２４０部分の壁の厚さは一般に一定
であるが、２７によって表わされる位置では、蝶番のよ
うに円周方向の線の周りに折れるよう環状の線の周りに
肉を取られている。即ちより小さい厚さに作られる。同
じように、軟らかい圧縮可能な先端部品２４は２８のと
ころで蝶番のようにカテーテルの端の外周辺に沿って折
れ曲がる。選択的に蝶番または折り曲がる線を作るよう
スリーブ壁部の厚さを小さくする代りに１周囲の材料よ
り異なった（より低い）剛性を有するようスリーブ材料
内に不連続部を持つことＫよって所期の折れ曲がる型を
達成することがまた可能である。Referring to FIG. 4, there is shown another preferred embodiment of a catheter having a distal end attached to a soft deformable catheter. As shown in FIG. 4, the tip part is a tubular sleeve 24 which surrounds the distal end of the catheter body 10 and fits thereto by a lap joint.
, the sleeve 24 extends a predetermined length beyond the distal end of the catheter. Rather than having a constant thickness, the walls of the resilient plastic sleeve 24 are such that when a predetermined small force is imposed on a stationary object, the furthest extremity or terminal end 25 of the sleeve is exposed to the pressure of FIG. It is formed in a shape that appears to have collapsed into the shape shown in the image above. More specifically, the wall thickness of the portion of the tip piece 240 that extends beyond the end of the catheter 10 is generally constant, but at the location represented by 27 it is bent around a circumferential line like a hinge. The meat has been removed around the circular line. That is, it is made to have a smaller thickness. Similarly, the soft compressible tip piece 24 is hinged at 28 around the outer periphery of the end of the catheter. Instead of reducing the thickness of the sleeve wall to create a selective hinge or fold line, it is possible to have a discontinuity in the sleeve material to have a different (lower) stiffness than one surrounding material. It is also possible to achieve a period bending mold.

軟らかい挫屈する先端２４を含むプラスティック材料の
荷重硬度を正しく選択することにより。By correctly selecting the load hardness of the plastic material containing the soft buckling tip 24.

その材料は記憶する性質を所有し、先端が最早静止物体
に向けておしつけられないときは、第４図に示される形
状に再び戻るであろう。例えば３゜において先端の中央
の開口２９を囲む材料の量を増加することがまた有利で
あることが分っている。The material possesses the property of remembering and will return to the shape shown in FIG. 4 when the tip is no longer forced towards a stationary object. It has also been found advantageous to increase the amount of material surrounding the central opening 29 of the tip, for example at 3°.

この材料の増加は、リングがたるむことを防ぐ開口を安
定化し強化するリングを画定する。This increase in material defines the ring which stabilizes and strengthens the aperture which prevents the ring from sagging.

第５図を参照して、先端部品が挫屈するとき。Referring to FIG. 5, when the tip part buckles.

それとそれがおしている物体との間の接触の有効面積は
増加させられ、それによってカテーテル構造によってそ
の組織に加えられる有効圧力は減小する。The effective area of contact between it and the object it is pushing on is increased, thereby reducing the effective pressure exerted by the catheter structure on the tissue.

別に限定することを意図したものでなくまたただ例示の
目的のためであるが、カテーテルの内腔は０．０４５イ
ンチ（１，１４１１１）の直径とその遠位末端で０．０
０８５インチ（０，２１６ｍ）の壁の厚さを有すること
ができる。第３図と第４図の軟らかい先端部品１８は好
適の場合は約０．００５インチ（０，１２７１％）の厚
さがあり１円形の蝶番の線２１０周すＣ’＆！約０．０
０４イ：ｙｆ　（０，１０２８）に小さくなる。遠位末
端は、この変形されていない状態では、約０．００１２
平方インチ（０，７７ｇ１１”　）あり、第５図のよう
に挫屈したときは面積で３．４１倍を表わす０．０１４
１平方インチ（２，６４ｗｎ２　）になる。Although not intended to be limiting and for illustrative purposes only, the lumen of the catheter has a diameter of 0.045 inches (1,14111 mm) and a diameter of 0.0 mm at its distal end.
It can have a wall thickness of 0.85 inches (0.216 m). The soft tip 18 of FIGS. 3 and 4 is preferably about 0.005 inches (0.1271%) thick and extends around one circular hinge line 210 C'&! Approximately 0.0
04i: yf becomes smaller to (0,1028). The distal end is approximately 0.0012 in this undeformed state.
square inch (0.77g11"), and when it buckles as shown in Figure 5, the area is 0.014 which represents 3.41 times the area.
1 square inch (2,64wn2).

第６図は、カテーテルがその遠位末端で、シラン系また
は他の軟らかく、変形可能なプラスティック材料から成
形される管状円筒形先端部品３１と嵌合するところのさ
らに別の実施例を示す。障害物におしつけられると、軟
らかいプラスティック先端は、この障害物に対して増カ
ルだ接触面積を与えるため拡張し曲がることによって変
形するであろう。FIG. 6 shows yet another embodiment in which the catheter is fitted at its distal end with a tubular cylindrical tip piece 31 molded from silane-based or other soft, deformable plastic material. When forced onto an obstacle, the soft plastic tip will deform by expanding and bending to provide an increased contact area with the obstacle.

本発明は特許法に従いまた新規の原理を適用するに必要
な情報をこの分野の技術に＃通の人に与えるため、また
必要な特別の部品を作り使用するため１以上かなり詳細
に記載される。しかしながら本発明は特に異なった機器
、装置によって実施され、また本発明は装置の詳細と操
作方法についての種々の変形として本発明自身の範囲か
ら外れることな〈実施できることが理解さるべきである
。The present invention is described in greater detail in accordance with patent law and in order to provide those skilled in the art with the information necessary to apply the novel principles and to make and use the special components necessary. . However, it is to be understood that the invention may be carried out in particular with different equipment and apparatus, and that the invention may be practiced with various modifications as to the details of the apparatus and its method of operation without departing from the scope of the invention itself.

【図面の簡単な説明】[Brief explanation of drawings]

第１図は従来の技術による血管造影用または診断用カテ
ーテルの遠位末端部を示す図；第２図はカテーテルに付
けたふくらますことのできる先端を有するカテーテルの
断面図；第３図は、ふくらますことのできる非膨張性先
端とこの先端と流体で連絡する弾性高分子材料のバンド
またはスリーブの断面図； 第４図は遠位末端において挫屈するスリーブを有する血
管造影用カテーテルの断面図で、スリーブは圧縮されな
い状態を図示する図； 第５図は第４図の一部断面図で、スリーブが挫屈した状
態を示す図； 第６図はカテーテルに付けた変形可能な先端の別の構造
の一部断面図である。 図において： １０・・・カテーテル本体、１１．１４・・・内腔（カ
テーテル）、１２・・・遠位床’４．１５・・・風船部
品。 １７・・・中央開口、１８・・・弾性高分子材料スリー
ブ。 ２４・・・チューブ状スリーグ 代理人　浅　村　皓Figure 1 shows the distal end of a prior art angiographic or diagnostic catheter; Figure 2 is a cross-sectional view of the catheter with an inflatable tip attached to the catheter; Figure 3 shows the inflatable tip attached to the catheter; FIG. 4 is a cross-sectional view of an angiography catheter having a sleeve that buckles at the distal end; FIG. FIG. 5 is a partial cross-sectional view of FIG. 4 showing the sleeve in a collapsed state; FIG. 6 shows an alternative configuration of the deformable tip attached to the catheter. It is a partially sectional view. In the figure: 10...catheter body, 11.14...lumen (catheter), 12...distal floor'4.15...balloon part. 17... Central opening, 18... Elastic polymer material sleeve. 24...Tubular three league agent Akira Asamura

Claims (1)

【特許請求の範囲】 ＋１１　カテーテルにおいて。 ｔａ＞長い弾性チューブ状部品は少なくとも１個のその
長さ全体にわたる内腔を含み；またｆｂ）軟かく変形可
能な先端部品は前記カテーテルの遠位末端に付けられ、
該先端部品は比較的静止した表面におしつけられると増
加した接触面積を与えることを特徴とするカテーテル。 （２、特許請求の範囲第１項に記載のカテーテルにおい
て。 前記先端部品は弾性のある膨張しない中空の流体を侵透
させないコンテナを含み、該コンテナの内部は前記内腔
と導通することを特徴とするカテーテル。 （３）　特許請求の範囲第２項に記載のカテーテルにお
いて。 前記コンテナはドーナツ形であることを特徴とするカテ
ーテル。 （４）特許請求の範囲の第１項に記載のカテーテルにお
いて。 前記変形可能な先端部品は前記カテーテルの遠位末端を
囲んでいることを特徴とするカテーテル。 （５）特許請求の範囲第２項に記載のカテーテルにおい
て。 前記先端部品は膨張しないポリオレフィン・プラストテ
ィックの膜材料で形成されることを特徴とするカテーテ
ル。 （６）特許請求の範囲第３項に記載のカテーテルにおい
て、カテーテルは前記ドーナツ形のコンテナの環状の開
口内に置かれる弾性プラスティックのＰ−ナラ形補強リ
ングをさらに含むことを特徴とするカテーテル。 （７）特許請求の範囲第１項に記載のカテーテルにおい
て。 前記変形可能な先端部品は、前記カテーテルの遠位末端
部分に付けられ、画風て決められた距離だけ末端を越え
て延びる弾性チューブ状スリーブを含み、その一部に環
状地域を有する弾性スリーブは前記先端部品の端が比較
的静止した表面に対しておしつけられたとき好適な折り
曲がる場所を作るため、前記カテーテルの前記遠位末端
を越えて延びることを特徴とするカテーテル。 （８）特許請求の範囲第ン項に記載のカテーテルにおい
て。 前記変形可能な先端部品は前記先端部品の前記端に開口
を有することを特徴とするカテーテル。 （９）　特許請求の範囲第８項に記載のカテーテルにお
いて。 前記開口は一体に成形した補強リングによって画定され
ることを特徴とするカテーテル。 Ｑｌ　特許請求の範囲第７項に記載のカテーテルにおい
て。 前記先端部品はポリウレタンで成形されることを特徴と
するカテーテル。 ａυ　特許請求の範囲第２項に記載のカテーテルにおい
て。 （ａ）膨張することのできる環状部の周辺の周り状部品
に封止するよう着けられる膨張することのできる環状部
。 （ｂ）前記膨張することのできる環状部の下方に前記チ
ューブ状部品の壁を貫通して形成される半径方向の側方
ボートを含み、該ポートは前記内腔と導通することを特
徴とするカテーテル。 （ｔり　特許請求の範囲第１１項に記載のカテーテルに
おいて。 前記膨張することのできる環状部は前記管状部品を取り
囲み、前記側方ボートを蔽う弾性高分子材料のバンドを
含むことを特徴とするカテーテル。 ａ３　特許請求の範囲第７項に記載のカテーテルにおい
て。 前記スリーブの外径は前記の長い弾性チューブ状部品の
外径と同じであることを特徴とするカテーテル。[Claims] +11 In a catheter. ta> an elongated elastic tubular component including at least one lumen extending throughout its length; and fb) a soft deformable tip component attached to the distal end of the catheter;
A catheter characterized in that the tip piece provides an increased contact area when pressed against a relatively stationary surface. (2. The catheter according to claim 1, wherein the tip part includes an elastic, non-expandable, hollow, fluid-impermeable container, and the interior of the container communicates with the lumen. (3) The catheter according to claim 2. The catheter is characterized in that the container is donut-shaped. (4) The catheter according to claim 1. 5. A catheter according to claim 2, wherein the deformable tip part surrounds the distal end of the catheter. (6) A catheter according to claim 3, characterized in that the catheter is formed of a flexible plastic membrane material placed within the annular opening of the donut-shaped container. - a catheter further comprising a oak-shaped reinforcing ring; (7) A catheter according to claim 1, wherein the deformable tip piece is attached to the distal end portion of the catheter; The elastic sleeve, which includes an elastic tubular sleeve extending beyond the distal end by a stylistically determined distance and having an annular region in a portion thereof, is suitable when the end of said tip piece is pressed against a relatively stationary surface. 8. A catheter according to claim 1, wherein the catheter extends beyond the distal end of the catheter to provide room for bending. A catheter according to claim 8, characterized in that it has an opening at said end of the component. (9) A catheter according to claim 8, characterized in that said opening is defined by an integrally molded reinforcing ring. Ql The catheter according to claim 7. The catheter characterized in that the tip part is molded from polyurethane. aυ The catheter according to claim 2. (a) Inflates. (b) an inflatable annulus that is fitted sealingly to the circumferential part around the periphery of the inflatable annulus; 12. A catheter according to claim 11, including a radial side boat formed therein, the port communicating with the lumen. A catheter according to claim 1, wherein the inflatable annulus includes a band of elastic polymeric material surrounding the tubular part and covering the lateral boats. a3 In the catheter according to claim 7. A catheter characterized in that the outer diameter of the sleeve is the same as the outer diameter of the elongated elastic tubular member.
JP58212297A 1983-08-08 1983-11-11 Catheter having deformable soft leading end Granted JPS6040069A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US06/520,996 US4531943A (en) 1983-08-08 1983-08-08 Catheter with soft deformable tip
US520996 1995-08-30

Publications (2)

Publication Number Publication Date
JPS6040069A true JPS6040069A (en) 1985-03-02
JPH0128588B2 JPH0128588B2 (en) 1989-06-05

Family

ID=24074909

Family Applications (1)

Application Number Title Priority Date Filing Date
JP58212297A Granted JPS6040069A (en) 1983-08-08 1983-11-11 Catheter having deformable soft leading end

Country Status (9)

Country Link
US (1) US4531943A (en)
JP (1) JPS6040069A (en)
CA (1) CA1207206A (en)
DE (1) DE3341850A1 (en)
DK (1) DK166129C (en)
FR (1) FR2550454B1 (en)
GB (1) GB2144635B (en)
IT (1) IT1171896B (en)
NL (1) NL187049C (en)

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Also Published As

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DK166129C (en) 1993-08-09
DE3341850C2 (en) 1990-08-09
FR2550454B1 (en) 1988-07-15
IT8349583A0 (en) 1983-12-27
IT1171896B (en) 1987-06-10
GB8330312D0 (en) 1983-12-21
DE3341850A1 (en) 1985-02-28
JPH0128588B2 (en) 1989-06-05
DK583083A (en) 1985-02-09
GB2144635A (en) 1985-03-13
DK583083D0 (en) 1983-12-16
US4531943A (en) 1985-07-30
DK166129B (en) 1993-03-15
NL8303940A (en) 1985-03-01
GB2144635B (en) 1987-04-23
NL187049C (en) 1991-05-16
FR2550454A1 (en) 1985-02-15
CA1207206A (en) 1986-07-08

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